|Publication number||US4784162 A|
|Application number||US 06/910,457|
|Publication date||Nov 15, 1988|
|Filing date||Sep 23, 1986|
|Priority date||Sep 23, 1986|
|Also published as||WO1988002237A1|
|Publication number||06910457, 910457, US 4784162 A, US 4784162A, US-A-4784162, US4784162 A, US4784162A|
|Inventors||Robert D. Ricks, Robert Bornn, David B. Hurt|
|Original Assignee||Advanced Medical Technologies|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (1), Non-Patent Citations (2), Referenced by (187), Classifications (12), Legal Events (9)|
|External Links: USPTO, USPTO Assignment, Espacenet|
1. Field of the Invention
The present invention relates to medical monitoring systems and, in particular, to a highly portable, non-invasive, physiological data telemetry recording system for monitoring sleep disorders.
2. Discussion of the Prior Art
Conventional practice for diagnosing sleep disorders requires that the patient be admitted to a "sleep lab". Typically, these sleep labs are located at hospitals or clinics and consist of a special in-patient unit equipped with a complicated array of cumbersome polysomnograph equipment. The patient is required to sleep in the unit while being monitored by a combination of bulky, uncomfortable sensors which are attached to various parts of the body. Obviously, the accuracy of the data generated under these circumstances is suspect because of the unfamiliar environment and physically uncomfortable circumstances in which the data is taken.
To eliminate the problems associated with "sleep labs", solid-state portable physiological monitoring systems have been developed for use in the patient's own environment.
One such system is available from Vitalog Corporation. The Vitalog system is a portable microcomputer which monitors information from up to eight physiological sensors. This information is processed and stored in on-board, solid-state memory for subsequent retrieval or display by a separate computer system.
The Vitalog system contains an eight-channel analog-to-digital interface and an R-wave detector. The multichannel A/D converter samples eight analog inputs. A one-channel motion sensor composed of an array of omnidirectional mercury tilt switches detects patient movement. A one-channel electrocardiogram (ECG) signal is monitored using three standard ECG electrode pads. The amplified ECG signal is connected to an A/D channel and also to the R-wave detection circuit. A temperature sensor array monitors three channels of temperature using standard probes. Either one or two channels of respiration may be monitored. One channel can be programmed to monitor a patient response button.
When the Vitalog system is activated, its ROM-based operating system continuously monitors the sensor inputs. After each programmed monitoring period, information relating to heart rate, physical activity and temperature is stored. A running mean of normal R-R intervals is calculated at the end of each heart beat. At the end of each monitoring period, the current mean is encoded into one of 16 levels (4 bits) and stored. A filtered output count from the motion sensor is accumulated and encoded into one of 8 levels (3 bits). Temperature information is encoded using a 3-bit tracking scheme.
The Vitalog system can store data from a minimum of 3600 epochs. Data compression is used to ensure that no memory is used when data is unchanging.
A fundamental shortcoming of the Vitalog system is that it lacks individual event resolution. That is, because data gathered over a full monitoring period must be stored in limited on-board memory for retrieval at the end of the monitoring period, the data must be compressed prior to storage. This requires pre-storage processing according to a predefined algorithm, further limiting the stored data characteristics to rigid identifying and modifying signatures, thus reducing analytical flexibility.
Thus, while the Vitalog system provides a screening tool, it does not address the need for a low cost, reliable, portable physiological data recording system which provides high data resolution for a number of parameters over long periods of time.
It is an object of the present invention to provide a low-cost, miniature, portable, physiological data monitoring system.
It is also an object of the present invention to provide a portable, physiological data monitoring system which will simultaneously monitor, transmit by radio and continuously record a virtually unlimited quantity of data relating to a plurality of physiological parameters.
It is a further object of the present invention to provide a physiological data recording system with high frequency data gathering capability for high individual event resolution.
These and other objects of the invention are accomplished by the physiological data monitoring system of the present invention which consists of a portable sensor unit which is worn by the patient to continuously gather and transmit data and a base station which stores the transmitted data for review and analysis.
The portable sensor unit includes a plurality of sensors, each of which monitors a physiological parameter and generates a corresponding electrical signal. In the preferred embodiment of the invention, the following parameters are monitored: left and right abdominal ECG, vertical position, rotational movement, patient activity level, breath sound, chest respiration and abdominal respiration; a nurse call button is also provided. The signal from each sensor is converted to a serial stream of digital data which is transmitted in real time as a low level radio signal by a digital telemetry transmitter.
The system base station includes a digital telemetry receiver which picks up the transmitted radio signal and provides it as digital data to a processing system for storage. In addition to high capacity memory, the base station also includes a standard I/O port for communication with other systems for review and analysis of the data.
FIG. 1 is a schematic block diagram illustrating the system of the present invention;
FIG. 2 is an illustration of the sensor unit of the system of the present invention;
FIGS. 3A and 3B combine to provide a schematic circuit diagram illustrating the analog portion of the sensor unit circuit of the system of the present invention;
FIG. 4 is a schematic circuit diagram illustrating the activity sensor portion of the sensing unit circuit of the system of the present invention;
FIGS. 5A and 5B combine to provide is a schematic circuit diagram illustrating the digital portion of the sensing unit circuit of the system of the present invention;
FIG. 6 is a schematic diagram illustrating the circuitry of the telemetry transmitter used in the system of the present invention; and
FIG. 7 is a schematic diagram illustrating the circuitry of the telemetry receiver used in the system of the present invention.
FIG. 1 shows a schematic block diagram of the monitoring system of the present invention.
A portable sensor unit 10, which is worn by the patient to be monitored, includes a number of sensors which continuously gather physiological data from the patient and generate corresponding electrical signals.
In the embodiment shown in FIG. 1, the physiologic data sensors include: an activity sensor 12, a breath-sound microphone 14, a chest respiration transducer 16, an abdominal respiration transducer 18, an oximeter 19, left and right electrocardiogram (ECG) electrodes 20 and 22, respectively, a vertical position sensor 24 and a rotational movement sensor 26. The sensor unit 10 also includes a manually operated, nurse call switch 28. The embodiment of the invention described herein also includes two spare sensor channels which could be used to monitor additional physiological parameters, but are presently used to provide warning signals indicating low battery power and an ECG "leads-off" condition, as described below.
The electrical signals generated by activity sensor 12, breath-sound microphone 14, the two respiration sensors 16 and 18 and oximeter 19 are analog signals which are provided to a multiplexer 30. Multiplexer 30 sequentially forwards these signals, together with the signals from the two spare channels, to an analog-to-digital converter 32 in response to clock signals provided by a system timer 34. The A/D converter 32 converts the analog input signal from the sensors to a binary data word which serves as the input to a serial encoder 36.
The signals from the left and right ECG electrodes 20 and 22 are provided to an ECG and R-wave detector 23. The output of R-wave detector 23, which is representative of the patient's heart beat rate, is provided to a counter 25 which generates a 2-bit heart beat signal to interface latch 38. The signals from vertical position sensor 24 and rotational movement sensor 26 are provided to a priority encoder 27 which provides a 4-bit signal representative of these parameters to interface latch 38, the signal from the vertical position sensor 24 being given priority. Nurse call switch 28 provides a 1-bit "on-off" signal to latch 38.
The 8-bit output of interface latch 38 comprises 7 bits of data from its just-described associated sensors and an additional system synchronization bit, set to 1, to inform the base station 44 of the beginning of a transmission sequence. The 8-bit output of A/D converter 32 also includes 7 data bits from its associated channels, the eighth bit being always set to zero to distinguish it from the synchronization bit of the interface latch output.
Serial encoder 36 converts each of the 8-bit parallel digital signals from A/D converter 32 and interface latch 38 to a serial data stream. The serial data stream is then provided to a digital telemetry transmitter 40 which transmits the uncompressed data by low-power radio signals at one-half second intervals to a telemetry receiver 42 of portable base station 44.
Thus, the complete transmission sequence is composed of eight channels, each 8 data bits wide, as described above. Each channel is composed of 12 synchronization pulses, a 7-bit address which identifies the channel and the 8 data bits.
The power for the sensor unit 10 is provided by a battery unit 46, which comprises four AAAA size batteries of 0.3" thickness. Use of these "quad-A" batteries allows the thickness of sensor unit 10 to be less than about 0.5 inches, making it relatively inobtrusive in comparison to prior art devices.
The radio signal received by telemetry receiver 42 is provided as a digital signal to CPU 48 which stores the data in memory 50 and/or communicates with additional peripheral devices via I/O port 58 for review and analysis of the data. The base station 44 also includes an LED display which verifies that data is being received and stored.
As shown in FIG. 2, sensor unit 10 includes a hybrid analog/digital circuit pack 100 which receives signals from the various sensors described above and provides these signals as a serial digital data stream to a second pack 102 which includes battery unit 46 and telemetry transmitter 40.
The circuit pack 100 and the battery/transmitter pack 102 are both attached to a body vest 104 by means of a VelcroŽ patch attached to the back of each unit 100, 102 and a corresponding patch attached to the vest 104. The vest 104 includes VelcroŽ patches for this purpose located both at the upper chest portion and at the abdominal portion so that the patient may attach the two packs 100 and 102 at the personally most comfortable location.
The hybrid circuit pack 100 receives the two respiration signals from two conventional respiration transducers 16 and 18 which are mounted around the patient's chest and abdomen, respectively. As shown in FIG. 2, each of the chest and abdominal respiration transducers 16 and 18 is formed as part of a body strap 106 and 108, respectively, which fits around the patient's torso to position the transducer at the desired location.
Two ECG electrodes 20 and 22 are attached to the patient, one at each side of the patient's chest area, and connected by shielded leads to the hybrid circuit pack 100. A third ground ECG electrode 21 is attached to the patient between the other two. In the preferred embodiment, the three ECG electrodes 20, 21 and 22 are connected to the inner side of chest respiration strap 106.
An electret microphone 14 is located at the patient's supersternal notch by means of a throat collar 110. Microphone 14 monitors the patient's breath sound and transmits a representative signal to the hybrid circuit pack 100.
A vibration piezo transducer 12 mounted on the patient's wrist by means of a bracelet 112 also provides its signal to the hybrid circuit pack 100.
The hybrid pack 100 further includes two position sensors 24 and 26 which, in the preferred embodiment, are mercury switches which monitor rotational movement and vertical position, respectively. A position switch 114 mounted at the bottom of the hybrid circuit box is used to normalize the body position of the patient when the position switch 114 is pressed. That is, when the position switch 114 is pressed, the patient's position at that time is defined as being "nose up", i.e., the patent is on his back with his nose in the vertical position. A nurse call button 28 is located at the top of the hybrid circuit pack 100 and may be activated by the patient.
FIGS. 3A and 3B provide a detailed circuit schematic diagram of the analog portion of sensor unit 10.
As shown in FIG. 3A, nodes N1 and N2 receive the left and right ECG signals, respectively, from left and right ECG electrodes 20 and 22 for the Heart Rate portion of the circuit. Node N3 is connected to center ECG/ground electrode 21. The ECG inputs from nodes N1 and N2 are provided to components 50 and 52, respectively, which together with component 54 form an instrumentation amplifier with a gain of approximately 1000. Transistors Q2 and Q3 form a "leads-off" detector circuit, where the base/emitter junction of transistor Q2 forms a fourth diode with clamping diodes D2, D3 and D4. This "leads-off" detector circuit operates with an external bias such that the conducting path is either from node N1 to ground node N3 or from node N1 to node N2 with the ECG leads connected. With the leads off, the current from ECG electrode 20 which is connected to node N1, is provided to the base of transistor Q2. This turns on both transistor Q2 and transistor Q3 and provides a high level output at node N4. This output is provided to one of the unused transmission channels, as mentioned above, to indicate that an ECG lead is disconnected.
A gain block composed of instrumentation amplifier 56, together with its feedback component, form a limiting amplifier with amplitude and slew rate limiting. The output of instrumentation amplifier 56 is zeroed by an autonull amplifier 57 which assures that the output of instrumentation amplifier 56 is forced quiescently toward zero. The output of instrumentation amplifier 56 is provided to a high pass formed by capacitor C26 and resistor R52 and also to a band pass filter 58. The output of band pass filter 58 is provided to a resistor divider formed by resistors R56 and R57 to ground and also to resistor R61 which is an input of amplifier 64. Amplifier 62 and its feedback circuitry receive the information from the output of amplifier 58 and capture that peak voltage onto capacitor C32. The voltage of capacitor C32 is then applied to the positive input of amplifier 64, the other input to amplifier 64 being provided through previously-mentioned resistor R61. The output of amplifier 64 through polarity blocking diode D8 forms a negative going waveform, which is the difference between the peak voltage applied at the positive input to amplifier 64 and the output of amplifier 58, and is applied through capacitor C34 to a comparator 60, the threshold of which is set by a divider provided by resistor R67 through resistor R66 to ground. Resistors R62 and R63 form positive feedback, or hysteresis, to assure clean switching of the output. The output of comparator 60 is then provided to node N5 which is the output pin of the Heart Rate, or ECG, circuit and the input to heart rate counter 25 shown in FIG. 1. The total of this aforedescribed circuitry forms R-wave detector 23 which provides one pulse per peak electrical QRS complex.
Referring now to the Breadth Sound section of FIG. 3B, resistor R1, capacitor C1 and resistor R70 form a bypass and bias network for electret microphone 14, the network then being connected back to node N6 of the circuit. The network around amplifier 66 forms a gain block and band pass filter which feeds a second gain block and band pass filter 68. The band pass of this network is approximately 300-900 Hz, while the network gain is approximately 500. The output of filter 68 is biased by resistor R5 toward the negative rail to allow full scale presentation of the breadth sound signal amplitude. This output is applied to resistor R7 and through diode D1. The peak waveform is captured across capacitor C8 to the negative rail with the discharge path through resistor R8 and parallel with capacitor C8 to output node N7 which is an input to multiplexer 30.
Referring now to FIG. 4, which shows the Activity portion of the circuit, the signal from the activity transducer 12 is received at node N8, provided to amplifier and low pass filter 70 and then to tracking comparator 72. The output of tracking comparator 72 is provided to non-retriggerable one-shot 74 which clocks out a digital signal to counter 76. The output of counter 76 is provided to a digital-to-analog converter 78, the output node N9 of which serves as an input to multiplexer 30. The counter 76 is reset to the 0 position by non-retriggerable one-shot 79 which is triggered by the falling edge of the transmitter enable signal, as described below.
Referring now to the Power Supply section of FIG. 3A, a 1.2 reference voltage 80 is provided to the negative input of amplifier 82. Transistor Q1, which is a series pass element, is operated in the inverted mode for low dropout characteristic. The feedback path for the regulator is through resistors R71 and R72 where nodes N10 and N11 are tied together for this application. Capacitor C36 forms an output compensation network to provide stability, since transistor Q1 is operating as a gain stage. Resistor R15 provides start-up current for the regulator.
Referring now to the Respiration section of FIG. 3B, the signals from both the abdominal and the chest transducers 18 and 16 are received at nodes N12 and N13, respectively. The signal received at node N12 is applied to capacitor C13 and to a boot strap amplifier 86 formed by booting resistors R17 and R19 to ground, where resistor R69 is brought off the center of this bootstrap configuration and provides a thousand megohm equivalent inputted impedance. The output of bootstrap amplifier 86 is applied through a gain block 88, the gain of which is set by resistors R22 and R24. The output of amplifier 88 is provided past one diode drop and again is reduced by the forward conductivity of diode D10, putting resistor R76 in parallel with resistor R24. Amplifier 90 and its associated circuitry provide an autonull loop for the output of bootstrap amplifier 88 which is sensed through resistor 26. The output of amplifier 90 is coupled back into amplifier 88 through resistor R25. The quiescent voltage of amplifier 88 is set by resistor divider R32 and R33 and is approximately -1.1 volts. Thus, the output of the abdominal transducer potion of the circuit is provided at node N14.
The chest transducer signal received at node N13 is similarly processed via amplifiers 86', 88' and 90' to provide a chest transducer output at node N15.
Referring now to the digital portion of the sensor unit circuitry shown in FIGS. 5A and 5B, the output of the Heart Rate circuitry of FIG. 3A is provided to node N16 and passes through diode D1 which shifts the level from positive to negative voltage. The logic requires only a positive to ground; therefore, diode D1 blocks the negative voltage and 4-bit counter 25 stores the heart rate count. This information is then provided to interface latch 38 as a 2-bit signal every one-half second during transmission.
A low voltage battery detector 94 provides its output on node N17 to one of the otherwise unused analog channels mentioned above. A low battery is, therefore, detected at base station 44.
A voltage converter 96 receives the voltage from the battery unit 46 and converts it to a negative voltage output. Therefore, node N18 of the digital hybrid circuit is the -4.5 voltage negative power supply point for the system.
Priority encoder 27 receives the signals from both position sensors 24 and 26, with the vertical position transducer receiving highest priority, and encodes it into four bits of binary weighted code. Nodes N19-N27 are the input pins from the position transducers.
Node N28 of the digital hybrid circuit switches the transmitter power supply and is gated from the output of the system enable timer 34. Thus, the signal at node N28 resets the one-shot 79 of the activity circuit.
Serial encoder 36 receives parallel digital data presented on its input pins and applies a serial output to the channel address at nodes 29-35, bringing these nodes either to ground or to the positive rail. Serial encoder 36 also produces an 8-bit serial data stream at node N36 which modulates transmitter 40.
Interface latch 38 switches in the digital information from its associated sensors during the digital channel transmission.
A/D converter 32 receives the output of analog multiplexer 30 and, upon command, digitizes each of the analog levels presented by multiplexer 30.
Transistors Q4 and Q5 are gated power supply devices which provide power to A/D converter 32.
FIG. 6 shows a detailed schematic circuit diagram of the digital telemetry transmitter 40.
As shown in FIG. 6, the serial data transmissions from encoder 36 are first modulated by a programmable data coder and then provided to a low pass filter. The filtered signals are then provided to a modulator, the output of which is forwarded to an oscillating section of the transmitter circuitry, the frequency determining element of which, i.e., crystal C100, has a resonant frequency of approximately 20 MHz. The outputs of the crystal C100 are amplified before exiting the oscillator section of the circuit and then forwarded to a first frequency tripler which triples the third harmonic of the oscillator output. The output of the first frequency tripler section is provided to a second frequency tripler section which generates the ninth harmonic of the oscillator output. The frequency of the output of the second tripler section is in the range of 180-212 MHz, which is known as the medical band. The outputs of the second tripler section are forwarded to the antenna elements of the transmitter 40 for transmission to the base station 44.
FIG. 7 shows a detailed schematic circuit diagram of the digital telemetry receiver 42. The signals transmitted from the transmitter 40 are received by the antenna elements of receiver unit 42. The signals received by the antenna elements are forwarded to an amplifier and summer network. The outputs of this network are forwarded to an RF amplifier, a mixer, and an amplifier and filter section. The output of the amplifier and filter section is provided to a serial decoder 47 which outputs an 8-bit digitized audio signal that is provided to CPU 48 for either storage in memory 50 or transmission through I/O port 58 to diagnostic equipment for analysis and review.
In the preferred embodiment, CPU 48 is an Hitachi 64180 microprocessor which directly addresses 512K of RAM and has a built-in R232C I/O port.
Data valid display 52 is an LED which is driven from a one-shot which is triggered by the data-valid port of serial decoder 47.
It should be understood that various alternatives to the embodiment shown herein may be employed in practicing the present invention. It is intended that the following claims define the invention, and that the structure within the scope of these claims and their equivalents be covered thereby.
|Cited Patent||Filing date||Publication date||Applicant||Title|
|US3815109 *||Jul 5, 1972||Jun 4, 1974||Nasa||Miniature multichannel biotelemeter system|
|1||*||Acitvity Sensors for Use in Psychiatric Evaluation, R. McPartland et al., IEEE Trans. on Bio Medical Eng., Mar. 1976.|
|2||*||Telemetry Instrumentation for Kinosiologic Studies of Knee Motion, D. Foster et al., Apr. 1980, Med Research Eng.|
|Citing Patent||Filing date||Publication date||Applicant||Title|
|US4981141 *||Feb 15, 1989||Jan 1, 1991||Jacob Segalowitz||Wireless electrocardiographic monitoring system|
|US4999772 *||Jan 24, 1989||Mar 12, 1991||Eden Tec Corporation||Sleep screening system with time based modulated data|
|US5168874 *||Aug 21, 1990||Dec 8, 1992||Jacob Segalowitz||Wireless electrode structure for use in patient monitoring system|
|US5280791 *||Oct 19, 1992||Jan 25, 1994||The Sleep Disorders Diagnostic And Treatment Center, Ltd.||Monitor system for determining the sleep stages of a person|
|US5307818 *||Jul 7, 1992||May 3, 1994||Jacob Segalowitz||Wireless electrocardiographic and monitoring system and wireless electrode assemblies for same|
|US5348008 *||Mar 19, 1992||Sep 20, 1994||Somnus Corporation||Cardiorespiratory alert system|
|US5353793 *||Nov 25, 1991||Oct 11, 1994||Oishi-Kogyo Company||Sensor apparatus|
|US5513646 *||May 9, 1994||May 7, 1996||I Am Fine, Inc.||Personal security monitoring system and method|
|US5549113 *||Jan 30, 1995||Aug 27, 1996||I Am Fine, Inc.||Apparatus and method for remote monitoring of physiological parameters|
|US5611349 *||May 11, 1995||Mar 18, 1997||I Am Fine, Inc.||Respiration monitor with simplified breath detector|
|US5617871 *||Dec 1, 1994||Apr 8, 1997||Quinton Instrument Company||Spread spectrum telemetry of physiological signals|
|US5704364 *||Nov 8, 1995||Jan 6, 1998||Instromedix, Inc.||Concurrent medical patient data and voice communication method and apparatus|
|US5719825 *||Nov 22, 1995||Feb 17, 1998||Biometrics, Inc.||Method for processing personal data|
|US5848027 *||Jan 27, 1998||Dec 8, 1998||Biometrics, Inc.||Method for processing personal data|
|US5919141 *||Sep 13, 1996||Jul 6, 1999||Life Sensing Instrument Company, Inc.||Vital sign remote monitoring device|
|US5928133 *||Mar 23, 1998||Jul 27, 1999||Halyak; George||User responsive sleep monitoring and awakening device|
|US5931791 *||Nov 5, 1997||Aug 3, 1999||Instromedix, Inc.||Medical patient vital signs-monitoring apparatus|
|US5941829 *||Oct 24, 1997||Aug 24, 1999||Instromedix, Inc.||Concurrent medical patient data and voice communication method and apparatus|
|US5942979 *||Apr 7, 1997||Aug 24, 1999||Luppino; Richard||On guard vehicle safety warning system|
|US6136274 *||Oct 7, 1997||Oct 24, 2000||Irori||Matrices with memories in automated drug discovery and units therefor|
|US6306088||Oct 3, 1998||Oct 23, 2001||Individual Monitoring Systems, Inc.||Ambulatory distributed recorders system for diagnosing medical disorders|
|US6329139||Aug 11, 1997||Dec 11, 2001||Discovery Partners International||Automated sorting system for matrices with memory|
|US6341229 *||Jun 7, 1999||Jan 22, 2002||Tapuz Medical Technology Ltd.||Wearable apron for use in egg and other medical tests|
|US6416471||Apr 15, 1999||Jul 9, 2002||Nexan Limited||Portable remote patient telemonitoring system|
|US6450953||Apr 15, 1999||Sep 17, 2002||Nexan Limited||Portable signal transfer unit|
|US6454708||Jun 9, 2000||Sep 24, 2002||Nexan Limited||Portable remote patient telemonitoring system using a memory card or smart card|
|US6494829||Apr 15, 1999||Dec 17, 2002||Nexan Limited||Physiological sensor array|
|US6605038||Jun 23, 2000||Aug 12, 2003||Bodymedia, Inc.||System for monitoring health, wellness and fitness|
|US6687523||Jul 6, 2000||Feb 3, 2004||Georgia Tech Research Corp.||Fabric or garment with integrated flexible information infrastructure for monitoring vital signs of infants|
|US6897788||Apr 17, 2002||May 24, 2005||Motorola, Inc.||Wireless system protocol for telemetry monitoring|
|US6987965||Oct 22, 2002||Jan 17, 2006||Motorola, Inc.||Programmable wireless electrode system for medical monitoring|
|US7020508||Aug 22, 2002||Mar 28, 2006||Bodymedia, Inc.||Apparatus for detecting human physiological and contextual information|
|US7071820 *||Mar 17, 2004||Jul 4, 2006||Callaway James J||Wireless patient ambulation motion detector and second call system|
|US7076435 *||May 20, 1994||Jul 11, 2006||Datex-Ohmeda, Inc.||Method for transferring patient information from a source monitor to a destination monitor|
|US7117035||Apr 1, 2004||Oct 3, 2006||Cardiac Pacemakers, Inc.||Subcutaneous cardiac stimulation system with patient activity sensing|
|US7171166||Oct 21, 2005||Jan 30, 2007||Motorola Inc.||Programmable wireless electrode system for medical monitoring|
|US7197357||Nov 30, 2001||Mar 27, 2007||Life Sync Corporation||Wireless ECG system|
|US7215991||Mar 24, 2003||May 8, 2007||Motorola, Inc.||Wireless medical diagnosis and monitoring equipment|
|US7261690||Aug 6, 2001||Aug 28, 2007||Bodymedia, Inc.||Apparatus for monitoring health, wellness and fitness|
|US7272428||May 16, 2003||Sep 18, 2007||Motorola, Inc.||Wireless electrocardiograph system and method|
|US7285090||Oct 9, 2003||Oct 23, 2007||Bodymedia, Inc.||Apparatus for detecting, receiving, deriving and displaying human physiological and contextual information|
|US7299964||Jan 15, 2004||Nov 27, 2007||Georgia Tech Research Corp.||Method and apparatus to create electrical junctions for information routing in textile structures|
|US7302294||Apr 2, 2004||Nov 27, 2007||Cardiac Pacemakers, Inc.||Subcutaneous cardiac sensing and stimulation system employing blood sensor|
|US7351208 *||Mar 12, 2004||Apr 1, 2008||Ge Medical Systems Information Technologies, Inc.||Respiration monitoring system and method|
|US7396333||Aug 18, 2003||Jul 8, 2008||Cardiac Pacemakers, Inc.||Prediction of disordered breathing|
|US7403808||Mar 11, 2005||Jul 22, 2008||Lifesync Corporation||Wireless ECG system|
|US7502643||Sep 13, 2004||Mar 10, 2009||Bodymedia, Inc.||Method and apparatus for measuring heart related parameters|
|US7555335||Apr 8, 2004||Jun 30, 2009||Cardiac Pacemakers, Inc.||Biopotential signal source separation using source impedances|
|US7570997||Apr 8, 2004||Aug 4, 2009||Cardiac Pacemakers, Inc.||Subcutaneous cardiac rhythm management with asystole prevention therapy|
|US7689437||Jun 16, 2000||Mar 30, 2010||Bodymedia, Inc.||System for monitoring health, wellness and fitness|
|US7698909||Feb 13, 2004||Apr 20, 2010||Nellcor Puritan Bennett Llc||Headband with tension indicator|
|US7715916||May 15, 2007||May 11, 2010||Cardiac Pacemakers, Inc.||Multi-parameter arrhythmia discrimination|
|US7785257 *||Jul 7, 2008||Aug 31, 2010||Home Guardian Llc||System and process for non-invasive collection and analysis of physiological signals|
|US7787946||Sep 17, 2004||Aug 31, 2010||Cardiac Pacemakers, Inc.||Patient monitoring, diagnosis, and/or therapy systems and methods|
|US7809420||Jul 26, 2006||Oct 5, 2010||Nellcor Puritan Bennett Llc||Hat-based oximeter sensor|
|US7810359||Oct 1, 2003||Oct 12, 2010||Nellcor Puritan Bennett Llc||Headband with tension indicator|
|US7813779||Jul 26, 2006||Oct 12, 2010||Nellcor Puritan Bennett Llc||Hat-based oximeter sensor|
|US7822453||Jul 28, 2006||Oct 26, 2010||Nellcor Puritan Bennett Llc||Forehead sensor placement|
|US7860557||Apr 13, 2005||Dec 28, 2010||Lifesync Corporation||Radiolucent chest assembly|
|US7865233||Feb 23, 2004||Jan 4, 2011||Cardiac Pacemakers, Inc.||Subcutaneous cardiac signal discrimination employing non-electrophysiologic signal|
|US7877126||Jul 26, 2006||Jan 25, 2011||Nellcor Puritan Bennett Llc||Hat-based oximeter sensor|
|US7877127||Jul 26, 2006||Jan 25, 2011||Nellcor Puritan Bennett Llc||Hat-based oximeter sensor|
|US7887493||Sep 13, 2004||Feb 15, 2011||Cardiac Pacemakers, Inc.||Implantable device employing movement sensing for detecting sleep-related disorders|
|US7899509||Jul 28, 2006||Mar 1, 2011||Nellcor Puritan Bennett Llc||Forehead sensor placement|
|US7933642||May 16, 2003||Apr 26, 2011||Rud Istvan||Wireless ECG system|
|US7938782||May 12, 2008||May 10, 2011||Cardiac Pacemakers, Inc.||Prediction of disordered breathing|
|US7978064||Jul 12, 2011||Proteus Biomedical, Inc.||Communication system with partial power source|
|US7979102||Feb 21, 2006||Jul 12, 2011||Nellcor Puritan Bennett Llc||Hat-based oximeter sensor|
|US7979122||Apr 8, 2004||Jul 12, 2011||Cardiac Pacemakers, Inc.||Implantable sudden cardiac death prevention device with reduced programmable feature set|
|US7996071||Jun 30, 2009||Aug 9, 2011||Cardiac Pacemakers, Inc.||Biopotential signal source separation using source impedances|
|US8002553||Aug 18, 2003||Aug 23, 2011||Cardiac Pacemakers, Inc.||Sleep quality data collection and evaluation|
|US8024039||Oct 17, 2007||Sep 20, 2011||Cardiac Pacemakers, Inc.||Subcutaneous cardiac sensing and stimulation system employing blood sensor|
|US8036748||Nov 13, 2009||Oct 11, 2011||Proteus Biomedical, Inc.||Ingestible therapy activator system and method|
|US8054140||Oct 17, 2007||Nov 8, 2011||Proteus Biomedical, Inc.||Low voltage oscillator for medical devices|
|US8055334||Dec 10, 2009||Nov 8, 2011||Proteus Biomedical, Inc.||Evaluation of gastrointestinal function using portable electroviscerography systems and methods of using the same|
|US8073707||Oct 11, 2005||Dec 6, 2011||Bodymedia, Inc.||System for detecting, monitoring, and reporting an individual's physiological or contextual status|
|US8114021||Dec 15, 2009||Feb 14, 2012||Proteus Biomedical, Inc.||Body-associated receiver and method|
|US8115618||May 23, 2008||Feb 14, 2012||Proteus Biomedical, Inc.||RFID antenna for in-body device|
|US8157731||Oct 9, 2003||Apr 17, 2012||Bodymedia, Inc.||Method and apparatus for auto journaling of continuous or discrete body states utilizing physiological and/or contextual parameters|
|US8255041||Feb 3, 2011||Aug 28, 2012||Lifesync Corporation||Wireless ECG system|
|US8257274||Sep 25, 2008||Sep 4, 2012||Nellcor Puritan Bennett Llc||Medical sensor and technique for using the same|
|US8258962||Mar 5, 2009||Sep 4, 2012||Proteus Biomedical, Inc.||Multi-mode communication ingestible event markers and systems, and methods of using the same|
|US8275635||Feb 19, 2008||Sep 25, 2012||Bodymedia, Inc.||Integration of lifeotypes with devices and systems|
|US8364220||Sep 25, 2008||Jan 29, 2013||Covidien Lp||Medical sensor and technique for using the same|
|US8369936||Feb 5, 2013||Bodymedia, Inc.||Wearable apparatus for measuring heart-related parameters and deriving human status parameters from sensed physiological and contextual parameters|
|US8382590||Feb 19, 2008||Feb 26, 2013||Bodymedia, Inc.||Entertainment, gaming and interactive spaces based on lifeotypes|
|US8398546||Sep 13, 2004||Mar 19, 2013||Bodymedia, Inc.||System for monitoring and managing body weight and other physiological conditions including iterative and personalized planning, intervention and reporting capability|
|US8403845||Jul 5, 2006||Mar 26, 2013||Bodymedia, Inc.||Wearable human physiological and environmental data sensors and reporting system therefor|
|US8412297||Jul 28, 2006||Apr 2, 2013||Covidien Lp||Forehead sensor placement|
|US8452367||Jul 26, 2010||May 28, 2013||Covidien Lp||Forehead sensor placement|
|US8515515||Mar 11, 2010||Aug 20, 2013||Covidien Lp||Medical sensor with compressible light barrier and technique for using the same|
|US8515535||Jan 28, 2010||Aug 20, 2013||Cardiac Pacemakers, Inc.||Implantable cardiac device with dyspnea measurement|
|US8535222||Mar 13, 2007||Sep 17, 2013||Cardiac Pacemakers, Inc.||Sleep detection using an adjustable threshold|
|US8540632||May 23, 2008||Sep 24, 2013||Proteus Digital Health, Inc.||Low profile antenna for in body device|
|US8540633||Aug 13, 2009||Sep 24, 2013||Proteus Digital Health, Inc.||Identifier circuits for generating unique identifiable indicators and techniques for producing same|
|US8540664||Mar 24, 2010||Sep 24, 2013||Proteus Digital Health, Inc.||Probablistic pharmacokinetic and pharmacodynamic modeling|
|US8542123||Aug 1, 2012||Sep 24, 2013||Proteus Digital Health, Inc.||Multi-mode communication ingestible event markers and systems, and methods of using the same|
|US8545402||Apr 27, 2010||Oct 1, 2013||Proteus Digital Health, Inc.||Highly reliable ingestible event markers and methods for using the same|
|US8545436||Dec 23, 2011||Oct 1, 2013||Proteus Digital Health, Inc.||Body-associated receiver and method|
|US8547248||Sep 1, 2006||Oct 1, 2013||Proteus Digital Health, Inc.||Implantable zero-wire communications system|
|US8558563||Aug 23, 2010||Oct 15, 2013||Proteus Digital Health, Inc.||Apparatus and method for measuring biochemical parameters|
|US8583227||Sep 23, 2011||Nov 12, 2013||Proteus Digital Health, Inc.||Evaluation of gastrointestinal function using portable electroviscerography systems and methods of using the same|
|US8585606||Sep 23, 2010||Nov 19, 2013||QinetiQ North America, Inc.||Physiological status monitoring system|
|US8597186||Jan 5, 2010||Dec 3, 2013||Proteus Digital Health, Inc.||Pharmaceutical dosages delivery system|
|US8606356||Aug 17, 2004||Dec 10, 2013||Cardiac Pacemakers, Inc.||Autonomic arousal detection system and method|
|US8657756||Feb 15, 2011||Feb 25, 2014||Cardiac Pacemakers, Inc.||Implantable device employing movement sensing for detecting sleep-related disorders|
|US8663106||Mar 22, 2005||Mar 4, 2014||Bodymedia, Inc.||Non-invasive temperature monitoring device|
|US8668653 *||Mar 24, 2005||Mar 11, 2014||Nihon Kohden Corporation||Biological information measuring garment having sensor, biological information measuring system and equipment, and control method of equipment|
|US8674825||Mar 13, 2009||Mar 18, 2014||Proteus Digital Health, Inc.||Pharma-informatics system|
|US8694330||Apr 1, 2009||Apr 8, 2014||The Invention Science Fund I, Llc||Methods and systems for presenting an inhalation experience|
|US8706518||Mar 25, 2009||Apr 22, 2014||The Invention Science Fund I, Llc||Methods and systems for presenting an inhalation experience|
|US8712794||Apr 27, 2009||Apr 29, 2014||The Invention Science Fund I, Llc||Methods and systems for presenting an inhalation experience|
|US8718193||Nov 19, 2007||May 6, 2014||Proteus Digital Health, Inc.||Active signal processing personal health signal receivers|
|US8721540||Nov 18, 2010||May 13, 2014||Proteus Digital Health, Inc.||Ingestible circuitry|
|US8725529||Feb 13, 2009||May 13, 2014||The Invention Science Fund I, Llc||Methods and systems for presenting an inhalation experience|
|US8730031||Jul 11, 2011||May 20, 2014||Proteus Digital Health, Inc.||Communication system using an implantable device|
|US8738395||Apr 21, 2009||May 27, 2014||The Invention Science Fund I, Llc||Methods and systems for presenting an inhalation experience|
|US8750992||Aug 15, 2013||Jun 10, 2014||Cardiac Pacemakers, Inc.||Implantable cardiac device with dyspnea measurement|
|US8771184||May 4, 2007||Jul 8, 2014||Body Science Llc||Wireless medical diagnosis and monitoring equipment|
|US8781548||Mar 11, 2010||Jul 15, 2014||Covidien Lp||Medical sensor with flexible components and technique for using the same|
|US8784308||Dec 2, 2010||Jul 22, 2014||Proteus Digital Health, Inc.||Integrated ingestible event marker system with pharmaceutical product|
|US8802183||Jul 11, 2011||Aug 12, 2014||Proteus Digital Health, Inc.||Communication system with enhanced partial power source and method of manufacturing same|
|US8810409||May 6, 2013||Aug 19, 2014||Proteus Digital Health, Inc.||Multi-mode communication ingestible event markers and systems, and methods of using the same|
|US8816847||Jun 3, 2011||Aug 26, 2014||Proteus Digital Health, Inc.||Communication system with partial power source|
|US8836513||Jul 11, 2011||Sep 16, 2014||Proteus Digital Health, Inc.||Communication system incorporated in an ingestible product|
|US8843196||Sep 20, 2011||Sep 23, 2014||Cardiac Pacemakers, Inc.||Subcutaneous cardiac sensing and stimulation system|
|US8847766||Apr 28, 2006||Sep 30, 2014||Proteus Digital Health, Inc.||Pharma-informatics system|
|US8856298||Feb 28, 2008||Oct 7, 2014||Corporacia Sanitaria Parc Tauli||Method and system for managing related-patient parameters provided by a monitoring device|
|US8858432||Feb 1, 2008||Oct 14, 2014||Proteus Digital Health, Inc.||Ingestible event marker systems|
|US8868453||Nov 4, 2010||Oct 21, 2014||Proteus Digital Health, Inc.||System for supply chain management|
|US8912908||Jul 11, 2011||Dec 16, 2014||Proteus Digital Health, Inc.||Communication system with remote activation|
|US8915741||Aug 23, 2011||Dec 23, 2014||Cardiac Pacemakers, Inc.||Sleep quality data collection and evaluation|
|US8926509||Jun 5, 2008||Jan 6, 2015||Hmicro, Inc.||Wireless physiological sensor patches and systems|
|US8932221||Mar 7, 2008||Jan 13, 2015||Proteus Digital Health, Inc.||In-body device having a multi-directional transmitter|
|US8939970||Feb 29, 2012||Jan 27, 2015||Vessix Vascular, Inc.||Tuned RF energy and electrical tissue characterization for selective treatment of target tissues|
|US8945005||Oct 25, 2007||Feb 3, 2015||Proteus Digital Health, Inc.||Controlled activation ingestible identifier|
|US8951251||Nov 7, 2012||Feb 10, 2015||Boston Scientific Scimed, Inc.||Ostial renal nerve ablation|
|US8954146||Apr 16, 2014||Feb 10, 2015||Cardiac Pacemakers, Inc.||Implantable cardiac device with dyspnea measurement|
|US8956287||May 2, 2007||Feb 17, 2015||Proteus Digital Health, Inc.||Patient customized therapeutic regimens|
|US8956288||Feb 14, 2008||Feb 17, 2015||Proteus Digital Health, Inc.||In-body power source having high surface area electrode|
|US8956295||Sep 9, 2013||Feb 17, 2015||Cardiac Pacemakers, Inc.||Sleep detection using an adjustable threshold|
|US8961412||Sep 25, 2008||Feb 24, 2015||Proteus Digital Health, Inc.||In-body device with virtual dipole signal amplification|
|US8961413||May 16, 2006||Feb 24, 2015||Bodymedia, Inc.||Wireless communications device and personal monitor|
|US8961414||Mar 15, 2007||Feb 24, 2015||Aliphcom||Apparatus for monitoring health, wellness and fitness|
|US8974451||Oct 25, 2011||Mar 10, 2015||Boston Scientific Scimed, Inc.||Renal nerve ablation using conductive fluid jet and RF energy|
|US9011327 *||Dec 18, 2008||Apr 21, 2015||Koninklijke Philips N.V.||Capacitive sensing and communicating|
|US9014779||Jan 28, 2011||Apr 21, 2015||Proteus Digital Health, Inc.||Data gathering system|
|US9014819||Nov 12, 2013||Apr 21, 2015||Cardiac Pacemakers, Inc.||Autonomic arousal detection system and method|
|US9023034||Nov 22, 2011||May 5, 2015||Boston Scientific Scimed, Inc.||Renal ablation electrode with force-activatable conduction apparatus|
|US9028404 *||Jul 28, 2010||May 12, 2015||Foster-Miller, Inc.||Physiological status monitoring system|
|US9028472||Dec 21, 2012||May 12, 2015||Vessix Vascular, Inc.||Methods and apparatuses for remodeling tissue of or adjacent to a body passage|
|US9028485||Sep 23, 2011||May 12, 2015||Boston Scientific Scimed, Inc.||Self-expanding cooling electrode for renal nerve ablation|
|US9033875||Oct 27, 2007||May 19, 2015||Bodymedia, Inc.||Multi-sensor system, device, and method for deriving human status information|
|US9037259||Dec 21, 2012||May 19, 2015||Vessix Vascular, Inc.||Methods and apparatuses for remodeling tissue of or adjacent to a body passage|
|US9046919||Aug 19, 2008||Jun 2, 2015||Hmicro, Inc.||Wearable user interface device, system, and method of use|
|US9050106||Dec 21, 2012||Jun 9, 2015||Boston Scientific Scimed, Inc.||Off-wall electrode device and methods for nerve modulation|
|US9060708||Jul 25, 2014||Jun 23, 2015||Proteus Digital Health, Inc.||Multi-mode communication ingestible event markers and systems, and methods of using the same|
|US9060761||Nov 9, 2011||Jun 23, 2015||Boston Scientific Scime, Inc.||Catheter-focused magnetic field induced renal nerve ablation|
|US9072902||Dec 21, 2012||Jul 7, 2015||Vessix Vascular, Inc.||Methods and apparatuses for remodeling tissue of or adjacent to a body passage|
|US9079000||Oct 16, 2012||Jul 14, 2015||Boston Scientific Scimed, Inc.||Integrated crossing balloon catheter|
|US9083589||Mar 6, 2014||Jul 14, 2015||Proteus Digital Health, Inc.||Active signal processing personal health signal receivers|
|US9084609||Jul 18, 2011||Jul 21, 2015||Boston Scientific Scime, Inc.||Spiral balloon catheter for renal nerve ablation|
|US9089350||Nov 9, 2011||Jul 28, 2015||Boston Scientific Scimed, Inc.||Renal denervation catheter with RF electrode and integral contrast dye injection arrangement|
|US9107806||Nov 18, 2011||Aug 18, 2015||Proteus Digital Health, Inc.||Ingestible device with pharmaceutical product|
|US20040152957 *||Oct 9, 2003||Aug 5, 2004||John Stivoric||Apparatus for detecting, receiving, deriving and displaying human physiological and contextual information|
|US20040153007 *||Jan 8, 2004||Aug 5, 2004||Shawn Harris||Physiological monitoring and system|
|US20040183684 *||Mar 17, 2004||Sep 23, 2004||Callaway James J.||Wireless patient ambulation motion detector and second call system|
|US20040230229 *||Jun 13, 2003||Nov 18, 2004||Lovett Eric G.||Hybrid transthoracic/intrathoracic cardiac stimulation devices and methods|
|US20040259270 *||Oct 31, 2003||Dec 23, 2004||Wolf David E.||System, device and method for exciting a sensor and detecting analyte|
|US20050119708 *||Feb 23, 2004||Jun 2, 2005||Paul Haefner||Subcutaneous cardiac signal discrimination employing non-electrophysiologic signal|
|US20050203431 *||Mar 12, 2004||Sep 15, 2005||Ge Medical Systems Information Technologies, Inc.||Respiration monitoring system and method|
|US20050245839 *||Mar 22, 2005||Nov 3, 2005||John Stivoric||Non-invasive temperature monitoring device|
|US20060031102 *||Oct 11, 2005||Feb 9, 2006||Bodymedia, Inc.||System for detecting, monitoring, and reporting an individual's physiological or contextual status|
|US20090281394 *||Sep 21, 2007||Nov 12, 2009||Brian Keith Russell||Bio-mechanical sensor system|
|US20100160746 *||Feb 8, 2010||Jun 24, 2010||Hmicro, Inc. A Delaware Corporation||Integrated Mobile Healthcare System for Cardiac Care|
|US20120029299 *||Jul 28, 2010||Feb 2, 2012||Deremer Matthew J||Physiological status monitoring system|
|CN100471445C||Mar 14, 2006||Mar 25, 2009||周常安||Paster style physiological monitoring device|
|EP1272109A1 *||Mar 23, 2001||Jan 8, 2003||ILife Systems Inc.||Physiological condition monitors utilizing very low frequency acoustic signals|
|EP2280639A2 *||May 26, 2009||Feb 9, 2011||Itamar Medical Ltd.||Method and apparatus for examining subjects for particular physiological conditions utilizing acoustic information|
|EP2280639A4 *||May 26, 2009||Sep 25, 2013||Itamar Medical Ltd||Method and apparatus for examining subjects for particular physiological conditions utilizing acoustic information|
|EP2353500A3 *||Jan 27, 2011||Jan 11, 2012||Nihon Kohden Corporation||Portable biological signal measurement/transmission system|
|WO1995030369A1 *||May 8, 1995||Nov 16, 1995||I Am Fine Inc||Personal security monitoring system and method|
|WO1999041647A1 *||Feb 11, 1998||Aug 19, 1999||Biometrics Inc||Method for processing personal data|
|WO2002022010A1||Sep 12, 2001||Mar 21, 2002||Nexan Ltd||Disposable vital signs monitoring sensor band with removable alignment sheet|
|WO2002102240A2 *||Jun 19, 2002||Dec 27, 2002||Digital Sports Media||Physiological monitoring and system|
|WO2009144721A2||May 26, 2009||Dec 3, 2009||Itamar Medical Ltd.||Method and apparatus for examining subjects for particular physiological conditions utilizing acoustic information|
|WO2014197604A3 *||Jun 4, 2014||Mar 12, 2015||President And Fellows Of Harvard College||Medical sensor providing audio communication tones|
|International Classification||A61B5/113, A61B5/00, A61B5/0205|
|Cooperative Classification||A61B5/0002, A61B5/0205, A61B5/1135, A61B5/6805|
|European Classification||A61B5/68B1D1, A61B5/00B, A61B5/0205, A61B5/113B|
|Jun 16, 1992||REMI||Maintenance fee reminder mailed|
|Nov 16, 1992||FPAY||Fee payment|
Year of fee payment: 4
|Nov 16, 1992||SULP||Surcharge for late payment|
|Jun 25, 1996||REMI||Maintenance fee reminder mailed|
|Nov 15, 1996||SULP||Surcharge for late payment|
|Nov 15, 1996||FPAY||Fee payment|
Year of fee payment: 8
|Jun 6, 2000||REMI||Maintenance fee reminder mailed|
|Nov 12, 2000||LAPS||Lapse for failure to pay maintenance fees|
|Jan 16, 2001||FP||Expired due to failure to pay maintenance fee|
Effective date: 20001115